EP2066402B1 - Implantierbare vorrichtung - Google Patents

Implantierbare vorrichtung Download PDF

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Publication number
EP2066402B1
EP2066402B1 EP07802328A EP07802328A EP2066402B1 EP 2066402 B1 EP2066402 B1 EP 2066402B1 EP 07802328 A EP07802328 A EP 07802328A EP 07802328 A EP07802328 A EP 07802328A EP 2066402 B1 EP2066402 B1 EP 2066402B1
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EP
European Patent Office
Prior art keywords
voltage
output
voltages
respect
electrical
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Not-in-force
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EP07802328A
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German (de)
English (en)
French (fr)
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EP2066402A2 (de
Inventor
Albrecht Rothermel
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Retina Implant AG
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Retina Implant AG
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Publication of EP2066402A2 publication Critical patent/EP2066402A2/de
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36046—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the eye

Definitions

  • the present invention relates to an implantable device which serves to deliver electrical stimulation signals to surrounding tissue via at least one stimulation electrode, with a sensor unit which generates a useful signal in the form of analogue voltage pulses from externally supplied signals, and an output stage which uses the useful signal Generates stimulation signals,
  • Such devices are widely used today to support or replace certain physiological functions of, for example, the human body, or to support sensory perceptions, for example, to make them possible again.
  • These devices include, but are not limited to, pacemakers, cochlear implants or retinal implants.
  • active retinal implants for implantation into the eye are provided with a plurality of stimulation electrodes that deliver electrical stimulation signals to cells of the retina to be contacted.
  • a plurality of picture elements converts incident light into the stimulation signals.
  • Such a retina implant is for example from the WO 2005/000395 A1 known.
  • the known retina implant serves to counteract loss of vision due to retinal degeneration.
  • the basic idea is to implant a microelectronic stimulation chip into a patient's eye, which replaces the lost vision with electrical stimulation of nerve cells.
  • the subretinal approach uses a stimulus chip implanted in the subretinal space between the outer retina and the retinal pigment epithelium, which converts incident ambient light into nerve cell stimulation signals onto an array of photodiodes integrated into the stimulation chip.
  • This retina implant thus stimulates the remaining, intact neurons of the degenerated retina, ie horizontal cells, bipolar cells, amacrine cells and possibly also ganglion cells.
  • the visual image impinging on the array of photodiodes or more complex elements is thus converted into an electrical stimulation pattern, which is then passed from the "natural computer" to the ganglion cells of the inner retina and from there via the optic nerve to the visual cortex.
  • the subretinal approach takes advantage of the natural interconnection of the formerly existing and now degenerate or lost photoreceptors the ganglion cells in order to supply the visual cortex in the usual way nerve impulses that correspond to the image seen.
  • the epiretinal approach uses a device consisting of an extra-ocular and an intra-ocular part, which communicate with each other in an appropriate manner.
  • the extra-ocular part comprises a camera and a microelectronic circuit for decoding captured light, ie the image information, and transmitting it as a stimulation pattern to the intra-ocular part.
  • the intra-ocular part contains an electrode array which contacts neurons of the inner retina and thus directly stimulates the ganglion cells located there.
  • the image information must be externally converted into a spatial and temporal stimulation pattern of electrical pulses so that they can be "understood" by the visual cortex.
  • the incident light is therefore converted into monophasic, anodic voltage pulses with a pulse length of about 500 microseconds and a pulse interval of preferably 50 msec, so that a repetition frequency of 20 Hz results proved to be sufficient for flicker-free vision; it also corresponds to the physiological flicker frequency at low ambient brightness.
  • the pulse spacing in the range of 50 msec is sufficient to be able to return the electrode polarization.
  • the output of the implant is connected to the electrical ground of the implant by means of a short circuit, so that the capacity of the Helmholtz double layer is discharged again and virtually no charge transport in the temporal average Fabric done.
  • cardiac pacemakers have long been available wireless implants that are powered by a co-implanted battery, due to the smaller dimensions of many other implants and the physiological limitations, for example, both retina and cochlear implants, the permanent external supply of energy required.
  • this external energy is either fed in by additionally irradiated non-visible light or inductively coupled externally, for example via a coil, or supplied via a cable.
  • That from the WO 2005/000395 A1 known implant is therefore supplied via irradiated IR light or inductively coupled RF energy wirelessly with electrical energy, which may be contained in this externally supplied external energy information for controlling the implant.
  • a retina implant powered only by ambient light that does not use external components for powering or providing image information.
  • the known implant comprises an implanted array of ambient light responsive photovoltaic cells which generate a supply voltage for a likewise implanted stimulation chip via which they are connected to an eye-going cable.
  • the stimulation chip comprises a number of pixels, each having a photosensitive circuit and an electrode connected thereto. Retina cells are stimulated by this electrode with biphasic pulses, which have a pulse duration of 1 ms and a repetition rate of 25 Hz.
  • the biphasic pulses should be designed so that they do not transport any charge in the surrounding tissue over the course of time.
  • the object of the present invention is to improve the delivery of the stimulation signals in the case of the device mentioned in the introduction, preferably in a simple circuit-wise manner.
  • this object is achieved in the device mentioned above in that the output stage emits the stimulation signals in the time average substantially DC-free to connect to the tissue external mass, and the device has a DC supply voltage and an electrical ground, which is substantially symmetrical to the external ground.
  • the inventors of the present application have recognized that the electrolytic decomposition processes in the surrounding tissue should be avoided not only in the area of the supply voltage supplying cable but also in the area of the stimulation electrodes.
  • the output stage comprises an inverter that supplies the stimulation signals to the stimulation electrode as a result of pulses having two different phases in each case.
  • the stimulation signals are DC-free with respect to time over the external ground in a circuit-wise simple manner can be given, because on the chip is now compared to the external ground - so the patient negative - voltage available.
  • the inverter represents a circuit-technically simple option for reversing the voltage pulses. Because of the biphasic, lying symmetrically to the external ground stimulation signals, the DC freedom already results over a very short period of time. Only during this period of time are successive voltages that could cause an electrolytic decomposition, but still within the short period of the biphasic pulse, an inverse voltage pulse is delivered.
  • the inverter has two parallel to each other between the output of the sensor unit and the stimulation electrode connected branches, both at its output each having a first, substantially rectangular electrical AC voltage connected first current mirror, wherein the one branch with a a second, substantially rectangular electric alternating voltage connected second current mirror, which is connected between the sensor unit and the first current mirror.
  • This measure is particularly advantageous circuit technology, it represents an elegant solution for the polarity reversal of the voltage pulses, while at the same time shows only a very low power consumption, especially since the inverter can be controlled via the phase change of the rectangular alternating voltages.
  • the inverter reverses the polarity of the voltage pulses in relation to the alternating voltages with respect to the external ground.
  • the device comprises an input stage, which can be connected to a supply unit, via which the device is supplied with electrical energy, wherein the supply unit is connected to the device via cables, via which it connects the input stage with at least one substantially rectangular electrical AC voltage supplied, which is at least almost DC-free with respect to a connectable to the tissue external mass in the time average.
  • the inventors of the present application have recognized that it is neither necessary to supply the implant with DC voltage nor that an AC voltage supply with appropriate rectification on the implant is required. If, instead, a substantially rectangular electrical alternating voltage is fed in as the supply, then the potential layer can be selected such that the supply voltage is at least virtually DC-free over the time average. In this way, on the supply side, the disturbing electrolytic decomposition processes are at least largely avoided.
  • the DC supply voltage then still consists of voltage pulses between which small voltage gaps occur because of the finite slope in the polarity changes, such a pulsed DC supply voltage can be used in particular for the electrical supply of the implants, if - as already mentioned - during the voltage gaps or - In each case, the electronics are switched off, which is most easily achieved by switching off the DC supply voltage at the output of the corresponding rectifier in each case.
  • the input stage can be designed to save space, since no smoothing or stabilization is required on the chip.
  • the input stage is supplied by the supply unit with at least two substantially rectangular electrical alternating voltages, which in relation to the external ground in temporal Means are at least almost DC-free, the AC voltages are shifted from each other in phase.
  • the input stage comprises a rectifier circuit which rectifies the AC voltages and adds them to a DC supply voltage.
  • both supply voltages have a pulse sequence of +1.5 V and -1.5 V with respect to the external ground, a DC supply voltage of 3 V can be generated on the chip compared to the electrical ground there.
  • the lower voltage swings of the two alternating voltages have the further advantage that, in addition to the supply voltage-free on average over time, only low voltages are present which could cause electrolytic decomposition.
  • the input stage is supplied with a first and a second alternating voltage which, at approximately the same curve shape and approximately equal amplitudes, run at least almost inversely to one another.
  • the rectifier circuit can be constructed very simply, since the externally supplied rectangular AC voltage is symmetrical, so that comparable or mirror-image circuits for the rectification of the two AC voltages can be used.
  • the rectifier circuit generates the DC supply voltage from the first and the second AC voltage such that their electrical ground and the DC supply voltage are symmetrical to the external ground.
  • the rectifier circuit has switches for the respective AC voltage, which are controlled via the respective other AC voltage.
  • the rectifier circuit comprises two branches each having two field-effect transistors connected in parallel at their output electrodes, wherein the output electrodes in the first branch form the electrical ground and the output electrodes in the second branch deliver the DC supply voltage, and wherein each field-effect transistor is connected at its input electrode with one of the two AC voltages and at its control electrode with the other of the two AC voltages.
  • This measure is a technically particularly simple and meaningful implementation of the above-described rectification, in which one AC voltage is switched in each case by the other AC voltage.
  • a switch field effect transistors are used, on the one hand have only a very low power consumption and on the other hand compared to the usual rectifier diodes have a very low forward voltage. In this way, it is possible to build from the two mutually offset by 180 ° in phase rectangular alternating voltages almost uniform uniform DC supply voltage, only at the edge transitions of the pulses arise voltage dips.
  • the output of the second branch is connected via a switch to the DC supply voltage, which is always open when the AC voltages change their polarity with respect to the external ground.
  • the small voltage gaps can be compensated, for example, by supplying the input stage with a second pair of mutually inverse, substantially rectangular alternating voltages, which is shifted in phase with respect to the first pair, this phase shift deviating from 180 °.
  • a DC voltage constant over time can then be generated without voltage dips.
  • the or each AC voltage has a trapezoidal voltage curve, with roof phases of constant voltage and short edge phases, in which the polarity changes with respect to the external ground, wherein the length of the roof phases in the range of at most 100 msec and the edge phases preferably at most 10th %, more preferably less than 1% but more than 0.05% of the roof phase.
  • the implant contained a grid of direct-to-stimulate electrodes spaced 280 microns apart.
  • pulse shape, pulse length and pulse repetition frequency could be set individually.
  • the retina of a blind patient was stimulated subretinally by electrodes with biphasic, anodic starting pulses of up to 4 msec duration.
  • biphasic, anodic starting pulses of up to 4 msec duration.
  • control signals can be derived directly from the AC voltage.
  • the sensor unit has at its output an output amplifier whose output is always switched off via a control signal when the alternating voltage changes its polarity with respect to the external ground.
  • the inverter has a switch at its output, which always connects the output to the external ground at short notice whenever a voltage pulse has ended, the amplitude of which is thus switched to the internal ground for the duration of the pulse interval.
  • the device is an active retina implant, whose sensor unit comprises a plurality of image cells, which converts incident light into electrical signals, wherein the sensor unit from the electrical signals, the useful signal in the form of analog voltage pulses of certain pulse length and certain Generated pulse intervals, the amplitudes of which distract from the respective intensity of the incident light.
  • FIG. 1 schematically an implantable device 10 is shown, wherein the dimensions are not reproduced to scale.
  • the device 10 is connected via a cable 11 to a supply unit 12, which the device 10 with electrical energy and supplied with control signals.
  • a supply unit 12 which the device 10 with electrical energy and supplied with control signals.
  • fastening tabs 14 are provided, with which the cable can be attached to the body of the person to which the implant 10 is implanted.
  • the device 10 may be any implant that stimulates nerve cells.
  • it is an active retina implant 15, which has as carrier a film 16 on which stimulation electrodes 17 are arranged for the delivery of stimulation signals to nerve cells.
  • the retina implant 15 off Fig. 1 is intended to be implanted in a human eye 18 which is in Fig. 2 is shown very schematically. For the sake of simplicity, only the lens 19 and the retina 21 are shown, into which the implant 15 has been implanted.
  • the implant 15 is preferably introduced into the so-called subretinal space which forms between the pigment epithelium and the photoreceptor layer. If the photoreceptor layer is degenerate or lost, the subretinal space forms between the pigment epithelium and the bipolar and horizontal cell layer.
  • the retina implant 15 is placed so that over the in Fig. 1 17 stimulation signals can be exerted on cells in the retina 21.
  • the beam path is seen at 23, is passed through the lens 19 to the implant 15, where the visible light 2 is converted into electrical signals, which are converted into stimulation signals.
  • the cable 11 is led out laterally out of the eye and fastened to the outside of the sclera with the fastening straps 14, before the cable leads on to the external supply unit 12.
  • the supply unit 12 is then fastened in a manner not shown in detail outside the eye, for example on the skull of the patient.
  • electrical energy is sent to the implant 10, wherein at the same time control signals can be transmitted, which influence the operation of the implant, as for example in the aforementioned WO 2005/000395 A1 is described, the content of which is hereby made the subject of the present application.
  • Fig. 3 is schematically the structure of the active retinal implant 15 from Fig. 1 shown.
  • an input stage 25 is first to recognize, which is supplied via the cable 11 from the outside external external energy.
  • the input stage 15 is connected to a sensor unit 26, which in this case has a plurality of image cells 27, which converts incident visible light into electrical signals, which are then delivered via the stimulation electrodes 17 indicated next to the respective image cells to neurons of the retina.
  • the processing of the useful signals generated by the image cells 27 takes place in an output stage 28, which generates the corresponding stimulation signals, which are then fed back to the sensor unit 26 and the stimulation electrodes 17.
  • FIG. 3 is merely a schematic representation of the retina implant 15 showing the logical structure, the actual geometric arrangement of the individual components may result, for example, in the immediate vicinity of each image cell 27 having an output stage.
  • the implant 15 is connected via an indicated at 29 external mass with the tissue into which the implant is introduced. Furthermore, there is an electric Mass 31 indicated, which is not connected to the external ground 29 in the embodiment shown.
  • Fig. 4 is the input stage 25 of the implant 15 off Fig. 3 shown in greater detail.
  • the rectifier circuit 34 has a first branch 41, which is connected at its output to the electrical ground 31, and a second branch 42, which provides the DC supply voltage 39 via the output 37.
  • the first branch 41 has two n-MOS field-effect transistors 43, 44, while in the second branch 42 two p-MOS field-effect transistors 45, 46 are provided.
  • two field-effect transistors 43, 44 and 45, 46 are connected in parallel at its output electrode 47, while the first rectangular AC voltage 32 and the other time the second rectangular AC voltage 33 is connected to the input electrodes 48.
  • the field effect transistors 43 and 44 are always turned on when the AC voltages 32 (at terminal 35) and 33 (at terminal 36) emits a negative pulse and, accordingly, the respective other AC voltage outputs a positive pulse to the control electrodes 49 is directed.
  • the external ground 29 is also located symmetrically between the electrical ground 31 and the DC supply voltage 37.
  • Fig. 6 is now schematically the sensor unit 26 and the associated output stage 28 of the implant 15 from Fig. 3 shown.
  • a picture cell 27 is shown, which is associated with only a single output stage 28.
  • the stimulation electrode 17 is located to the right of the output stage 28, in the actual geometric arrangement However, the stimulation electrode 17 may be arranged next to or in the image cell 27.
  • the image cell 27 now has at its output an output amplifier 51 which is connected to a photodiode 52 for local brightness and another photodiode 53 for global brightness.
  • the amplifier 51 outputs at its output 54 a signal D, which corresponds in amplitude to the brightness of the light falling on the local photodiode 52, but which has been readjusted via the global brightness (photodiode 53).
  • the exact structure of a picture cell is analogous to that in the WO 2005/000395 A1 described image cells, so that may be referenced for further information on this document.
  • the output amplifier 51 is still connected to a control signal F at its input 55, via which the output signal D at the output 54 can be clocked in a manner to be described.
  • the output amplifier 51 is followed by an output current mirror 56 which mirrors the current flowing in the output amplifier 51 and thus also simultaneously conducts this to an inverter 57 which is provided in the output stage 28.
  • the inverter 57 has two current mirrors 58, 59, which are connected to the first AC voltage 32 and are connected at their output to the stimulation electrode 17.
  • a further current mirror 61 is provided, which is connected to the DC supply voltage 33 and connected between the image cell 27 and the current mirror 59.
  • the inverter 57 constructed in this way ensures that the current pulses D are reversed in synchronism with the phase change of the AC voltages 32, 33, so that stimulation signals E are available at the stimulation electrode 17 which are DC-free on a time average.
  • a switch 62 is still connected, which is controlled via a provided on the terminal 63 control signal G and the stimulation electrode 17 connects to the external ground 29.
  • Shown schematically is still a tissue 64 to which the stimulation signals E are delivered.
  • a series connection of an ohmic resistor 65 and a capacitor 66 is selected, which represents the Helmholtz double layer forming as a result of the electrode polarization.
  • the retinal implant 15 described so far is thus supplied on the one hand with DC-free voltage over alternating voltages 32, 33, and on the other hand it also emits a DC-free excitation signal E to surrounding tissue on a time average.
  • the retina implant 15 still requires the control signals F for switching the useful signal D and the control signal G for switching the stimulation signal E.
  • These signals can be derived on the chip from the alternating voltages 32 and 33, on the other hand also possible is to supply them also via the cable 11, namely in separate lines.
  • control signals can be used for current control.
  • the control signals can be coupled via a separate input circuit on the retina implant 15, which causes a small input impedance and provides a high-impedance output, can be fed via the in different loads. In this way, the control signals can be externally supplied without the risk of electrolytic decomposition.
  • the signal of the global photodiode 52 which serves to adapt the signal to the ambient brightness in a manner known per se.
  • This signal for the Ambient brightness can be generated either on the chip itself, as in the WO 2005/000395 A1 is described, but the signal can also be supplied externally via a separate cable in the manner described above.
  • the current flowing from the output current mirror 56 into the output amplifier 51 due to the useful signal D is now likewise mirrored in the inverter 57, in which case it flows either into the current mirror 58 or into the current mirror 61, since only one of these two current mirrors is currently with an alternating voltage connected, which shows a negative pulse.
  • the DC supply voltage 39 (Vcc) to +1.5 V
  • the electrical ground 31 to -1.5 V.
  • the current mirror 61 to -1.5 V, so that the current flows from the output current mirror 56 into the current mirror 61.
  • the mirrored current flows from the current mirror 59, because this is connected to the other AC voltage 32, the positive pulse is also +1.5 V.
  • This current is mirrored again and thus flows from the current mirror 59 into the external ground 29.
  • the implant 15 is supplied with two alternating voltages 32 and 33, which have a trapezoidal time characteristic and in each case lie symmetrically with respect to the external ground 29.
  • the two AC voltages 32 and 33 are Furthermore, inverse to each other, so they have a phase shift of 180 ° with each other.
  • the individual voltage pulses have a roof phase 68 of, for example, 20 msec and a flank phase 69 of, for example, 1 msec.
  • a roof phase 68 of, for example, 20 msec and a flank phase 69 of, for example, 1 msec are used.
  • the voltage C at the output 37 has a pulsed profile, in each case in the event of a phase change, the voltage collapses, which is represented by a voltage dip 71.
  • This voltage dip 71 is created by the use of the field effect transistors 43, 44, 45, 46, while conventional rectifier diodes in bridge circuit would not force this voltage dip.
  • the components following in the respective circuit can cope with this voltage dip, whereby the switch 38 can additionally be provided to disconnect the output 37 from the DC supply voltage 39 during the voltage dips 71, so that it can remain constant.
  • the image cell 27 initially generates a long pulse whose amplitude corresponds to the intensity of the light falling on the photodiode 52.
  • this output signal is now not delivered as a continuous pulse, but the amplifier 51 is clocked via the control signal F, which has two symmetrically to the edges 59 extending control pulses 72.
  • the useful signal D is divided into two voltage pulses 73, which are symmetrical to the edges of the AC voltages 32, 33.
  • the stimulation signal E results, which comprises a cathodic preparation pulse 74 opposite to the external mass 29 and an anodic excitation pulse 75 with respect to the external mass 29.
  • the stimulation signal E thus represents a biphasic excitation for the surrounding tissue 64, the excitation starting with a cathodic pulse.
  • a larger edge 76 is available for the excitation signal, resulting in a short-term high current flow into the surrounding tissue 64, so that a good excitation of the subsequent nerve cells is achieved.
  • the switch 62 is momentarily closed via the control signal G, so that the capacitor 66 discharges. It is important that the switch 62 connects to the external ground 29.
  • the stimulation signal E is free of DC voltage over time, and on the other hand it is also ensured that all the charge that has flowed into the tissue is returned, so that an excitation can be made again with the next following useful signal D.

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  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)
  • Electrotherapy Devices (AREA)
EP07802328A 2006-09-26 2007-09-15 Implantierbare vorrichtung Not-in-force EP2066402B1 (de)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102006047118A DE102006047118B4 (de) 2006-09-26 2006-09-26 Implantierbare Vorrichtung
PCT/EP2007/008045 WO2008037363A2 (de) 2006-09-26 2007-09-15 Implantierbare vorrichtung

Publications (2)

Publication Number Publication Date
EP2066402A2 EP2066402A2 (de) 2009-06-10
EP2066402B1 true EP2066402B1 (de) 2012-12-05

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US (1) US8612017B2 (ja)
EP (1) EP2066402B1 (ja)
JP (1) JP5171828B2 (ja)
DE (1) DE102006047118B4 (ja)
WO (1) WO2008037363A2 (ja)

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JP4310247B2 (ja) 2004-07-23 2009-08-05 株式会社ニデック 視覚再生補助装置
US7190153B2 (en) * 2004-12-01 2007-03-13 Alfred E. Mann Foundation For Scientific Research System, circuit and method for tuning a resonant circuit
CA2614604A1 (en) 2005-07-08 2007-06-28 Med-El Elektromedizinische Geraete Gmbh Cmos full wave rectifier
JP4952000B2 (ja) 2006-02-27 2012-06-13 ソニー株式会社 光装置およびその製造方法、並びに光機器

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US20090222063A1 (en) 2009-09-03
DE102006047118B4 (de) 2010-09-09
WO2008037363A2 (de) 2008-04-03
US8612017B2 (en) 2013-12-17
JP2010504179A (ja) 2010-02-12
WO2008037363A3 (de) 2008-12-11
DE102006047118A1 (de) 2008-04-17
EP2066402A2 (de) 2009-06-10
JP5171828B2 (ja) 2013-03-27

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